EP1125095B1 - Interferometers for optical coherence domain reflectometry and optical coherence tomography using nonreciprocal optical elements - Google Patents
Interferometers for optical coherence domain reflectometry and optical coherence tomography using nonreciprocal optical elements Download PDFInfo
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- EP1125095B1 EP1125095B1 EP99948162A EP99948162A EP1125095B1 EP 1125095 B1 EP1125095 B1 EP 1125095B1 EP 99948162 A EP99948162 A EP 99948162A EP 99948162 A EP99948162 A EP 99948162A EP 1125095 B1 EP1125095 B1 EP 1125095B1
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
- G01B9/00—Measuring instruments characterised by the use of optical techniques
- G01B9/02—Interferometers
- G01B9/0209—Low-coherence interferometers
- G01B9/02091—Tomographic interferometers, e.g. based on optical coherence
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
- G01B9/00—Measuring instruments characterised by the use of optical techniques
- G01B9/02—Interferometers
- G01B9/02015—Interferometers characterised by the beam path configuration
- G01B9/02022—Interferometers characterised by the beam path configuration contacting one object by grazing incidence
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/47—Scattering, i.e. diffuse reflection
- G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
- G01B2290/00—Aspects of interferometers not specifically covered by any group under G01B9/02
- G01B2290/35—Mechanical variable delay line
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
- G01B2290/00—Aspects of interferometers not specifically covered by any group under G01B9/02
- G01B2290/70—Using polarization in the interferometer
Definitions
- OCT Optical Coherence Tomography
- OCT is a novel imaging technique which allows for noninvasive cross-sectional imaging in scattering or cloudy media with high spatial resolution and high dynamic range.
- OCT is a two-dimensional extension of Optical Coherence-Domain Reflectometry (OCDR) which is also commonly referred to as Optical Low Coherence Reflectometry (OLCR), in which a low temporal coherence light source is employed to obtain precise localization of reflections internal to a probed structure along the optic axis.
- OCDR Optical Coherence-Domain Reflectometry
- OLCR Optical Low Coherence Reflectometry
- the one-dimensional ranging technique of OCDR/OLCR has previously been utilized for characterization of bulk-, integrated-, and fiber-optic structures, as well as biological tissues.
- this technique is extended to provide for scanning of the probe beam in a direction perpendicular to the optic axis, building up a two-dimensional data set comprising a cross-sectional image
- OCT has previously been applied to imaging of biological tissues in vivo and in vitro, although the majority of initial biomedical imaging studies concentrated on transparent structures such as the eye.
- Initial ophthalmic imaging studies demonstrated significant potential for OCT imaging in routine examination of normal and abnormal ocular structures, including imaging of the cornea, iris, and other structures of the anterior eye; the lens and lens capsule; and numerous structures in the posterior eye, including the neurosensory retina, retinal nerve fiber layer, retinal pigment epithelium, and choroid.
- OCT examination of the retina initial in vivo clinical studies have demonstrated its utility in aiding diagnosis in a variety of vitreoretinal diseases, including macular hole, macular degeneration, detached retina, and glaucoma.
- Clinical trials of OCT imaging for ophthalmic applications are currently under way at several centers, and a commercial ophthalmic OCT scanner is available from Humphrey Systems of Dublin, California.
- OCT optical coherence tomography
- OCT system implementations featuring the high-speed imaging acquisition necessary for in vivo application and catheter/endoscopic delivery have been reported.
- the application of OCT to biomedical imaging provides the potential for sub-surface tissue characterization with sufficient resolution to provide microscopic morphological information relevant to pathological diagnosis without the need for biopsy.
- OCT imaging may be useful for on-line process control or product testing and evaluation.
- Initial experiments have demonstrated OCT imaging in ceramic and other highly scattering materials, as well as for the characterization of the surface topology of opaque industrial materials such as metals (i.e., ball bearings).
- Optical coherence tomography performs micron-scale topographic imaging of internal tissue microstructure using a combination of the principles of low-coherence interferometry and confocal microscopy.
- Fig. 1 illustrating an exemplary OCT system 10 in which the tissue to be examined is placed in the sample arm 12 of a Michelson interferometer illuminated by a broadband light source 16. Due to the limited coherence length of the source (typically 10-15 microns), light returning from the reference arm 18 and light backscattered by internal sample reflections interferes constructively or destructively only when the interferometer arm optical path lengths are matched to within the source coherence length.
- a beamsplitter 20, optical detector 22, transimpedance amplifier 24, demodulator 26, A/D converter 28, and display 30 are also shown.
- the detector current generated by a sample containing multiple reflecting sites distributed along its depth contains the sum of multiple, overlapping copies of this interference pattern.
- a map of tissue reflectivity versus depth or "A-Scan" is obtained by scanning the reference mirror 32 at constant velocity, while recording the envelope of the detector current.
- the envelope may be recorded with high dynamic range by scanning the reference mirror 32 at fixed velocity, and demodulating the detector current at the resulting Doppler frequency.
- Cross-sectional images of tissue backscatter or "B-Scans" may be acquired by obtaining sequential A-scans while scanning the probe beam across the tissue surface using a lateral beam scanning mirror 33 or some other lateral scanning optic device.
- the resulting two-dimensional datasets are plotted as gray-scale or false-color images.
- the interferometer 14 acts as an optical heterodyne detector, providing a dramatic expansion in dynamic range compared to direct detection of scattered light. Since the interferometric component of the detector current is proportional to the product of the electric field amplitudes returning from each arm, the detected envelope signal is proportional to the square root of the sample power reflectivity. Extremely faint reflections in the sample ( ⁇ 10 -11 times the incident optical power) are routinely detected in A-scans recorded in a fraction of a second. As illustrated in Fig. 1 , the interferometer 14 can also be implemented using inexpensive semiconductor sources and detectors, and flexible single-mode optical fibers suitable for remote imaging through minimally invasive diagnostic instruments.
- a significant limitation in the use of OCDR and OCT in highly scattering media is that the OCT probe light is very strongly (exponentially) attenuated in the scattering material, thus limiting the imaging depth which can be achieved in a given amount of time for a given sensitivity.
- SNR signal to noise ratio
- SNR ⁇ ⁇ P s ⁇ R s 2 ⁇ qB
- SNR signal-to-noise ratio (a measure of the sensitivity which also relates to imaging depth in scattering media)
- ⁇ the detector responsivity
- P s the optical power incident on the sample
- R s the optical power reflectivity of the sample
- q the charge on the electron
- B the detector bandwidth.
- B is inversely proportional to the time required to obtain an OCDR scan or OCT image.
- the shot-noise limit under which this expression is calculated is well known to those practiced in the art to be the best possible performance (i.e., to give the best value for S/N) which can be achieved in an optical detection system.
- Equation (1) makes clear that there is a trade-off between sensitivity or depth, imaging time, and the source power incident on the sample in OCDR and OCT.
- Increases in imaging speed may only be achieved through either a decrease in S/N or an increase in power incident on the sample.
- Increases in sensitivity or imaging depth may only be obtained by increasing either the imaging time or the power on the sample.
- new technology has been developed permitting OCT image acquisition up to video rate (30 images/second), and high power low-coherence sources have become available to partially compensate for the decrease in sensitivity which necessarily accompanies any increase in imaging speed according to Eq. (1).
- these high power sources are very expensive, and still are not sufficiently powerful to allow for clinically acceptable quality imaging at video rate (or even at the ⁇ 10 images/second rate common to ultrasound imaging).
- the first requirement is that the total optical power incident on the detector 22 cannot be arbitrarily high in order for shot noise to dominate over excess intensity noise for available sources. For systems with optical sources 16 which emit low power, this is not a problem.
- recent developments in source technology have resulted in the availability of higher power sources (10-20 mW) which are very attractive for high-speed imaging since the higher sample arm power partially compensates for the increased bandwidth B necessary for higher speed imaging, according to Eq. (1). Since most industrial and biological samples have very low reflectivity, they do not reflect an appreciable amount of sample arm light power onto the detector 22.
- the second requirement on the amount of power on the detector is that it must be sufficiently high so that shot noise dominates over thermal noise in the detector.
- the power on the detector must be at least approximately 1 ⁇ W for a typical low speed system using a detector with a bandwidth less than approximately 100 kHz, to 10 ⁇ W for a typical high speed system using a detector with a bandwidth of approximately 10 MHz.
- the central element of the Michelson interferometer is a standard beamsplitter 20 which transmits or splits some fraction of the power (typically 50%) of the incident light power into each of the sample and reference arms 12 and 18.
- the beamsplitter 20 may be a mirror with a partially reflective coating, while in a fiber optic interferometer the beamsplitter is composed of a pair of fibers partially fused together which is known as a fiber coupler.
- the beamsplitter may be abstracted as a four-port optical element with two inputs (labeled as 11 and 12), and two outputs (labeled as O1 and O2).
- the abstracted beamsplitter illustrated in Fig. 2 is characterized by a splitting ratio ⁇ , such that a fraction ⁇ of the light power incident at port 11 (neglecting small internal losses of the beamsplitter) is transmitted to port O2, while the fraction (1- ⁇ ) of the light power incident at port I1 is transmitted to port O1.
- a splitting ratio ⁇ such that a fraction ⁇ of the light power incident at port 11 (neglecting small internal losses of the beamsplitter) is transmitted to port O2, while the fraction (1- ⁇ ) of the light power incident at port I1 is transmitted to port O1.
- This conventional beamsplitter is known as a reciprocal optic element because light which is input into either of the output ports O1 or O2 will reciprocally be transmitted to the input ports I1 and I2. Specifically, a fraction ⁇ of any light power incident at port O1 is transmitted to port I2, while the fraction (1- ⁇ ) of the light power incident at port O1 is transmitted to port I1. Finally, a fraction ⁇ of any light power incident at port O2 is transmitted to port I1, while the fraction (1- ⁇ ) of the light power incident at port O2 is transmitted to port I2.
- the light from the broadband source 16 is split evenly between the sample and reference arms, while light returning from both the sample and reference arms is split again into the input arms 34 and 36 containing the source 16 and detector 22.
- the detected signal power is proportional to the product of the 50% splitting ratio from the source 16 to the sample arm 12, and the 50% splitting ratio from the sample arm 12 to the detector 22, for a combined sample power double splitting ratio of 25%.
- Fiber couplers with coupling ratios other than 50% are commonly available; however, their use in the Michelson configuration is even worse. For example, if a 90/10 beamsplitter directs 90% of the source light into the sample arm and only 10% of the light into the reference arm, then the combined sample power splitting ratio is only 9% (10% of the 90% of the source light power incident on the sample).
- ⁇ the coupler splitting ratio
- P o the source power.
- WO 97/32182 A1 discloses in Figure 3 an interferometer for OCT based on a Mach-Zehnder interferometer (MZI) design using fiber couplers at the input and output ends.
- the couplers may be 50/50 couplers or configured to provide an uneven split.
- An optical circulator is arranged in each arm of the MZI. The circulator in one arm routes the optical path in that arm to a reference mirror and back. The circulator in the other arm routes the optical path in that arm to a sample and back.
- a dual balanced receiver is arranged at the output of the MZI to collect the signal.
- the invention which is described in several embodiments, consists of novel interferometer designs for OCDR and OCT which employ non-reciprocal optical elements in order to make more efficient use of the source light power.
- optical circulator 50 is a three-port optical device in which all power incident on input port I1 (except for small internal losses) is directed into output port O1 which is common with the second input port I2. All light incident on the input port I2 (except for small internal losses) is similarly directed into the output port O2.
- Polarization-independent optical circulators are commercially available, in which the performance is independent of the polarization state of the light at the input or output ports.
- Fiber-optic versions are particularly suitable for use in fiber-optic implementations of OCDR and OCT.
- An example of a commercially available fiber-optic optical circulator which would be suitable for use in the designs disclosed in this application is Model #60-13-3 from Princeton Optics, Inc., of Ewing, New Jersey.
- a second nonreciprocal optical element suitable for use in improving the performance of OCDR and OCT is the Faraday rotator.
- a Faraday rotator is a device which rotates the polarization state of a light beam which traverses it, by an angle which is a characteristic (fixed or variable) property of the rotator.
- a polarization-dependent form of optical circulator 52 may be constructed from a 45° Faraday rotator 54 and a polarizing beamsplitter (PBS) 56, as illustrated in Fig. 4 .
- PBS polarizing beamsplitter
- a polarizing beamsplitter 56 is an optical device which either transmits or reflects light incident upon it depending upon the polarization state of the incident light. As illustrated in Fig.
- the device illustrated in Fig. 4 is just one possible implementation of an optical circulator, and this is not an optimal implementation in many cases because the polarization state of the light entering port 12 must match the polarization state of the light exiting port O1, thus the sample must preserve polarization.
- Optical circulators are commercially available which allow for arbitrary polarization states at any of the input ports I1 or I2.
- this implementation may be used whenever the sample does in fact preserve the polarization state of the light reflected from it, and this implementation may in fact be less expensive than the alternative in that case.
- polarizing beamsplitter and a Faraday rotator suitable for use in the designs disclosed in this application are Model #10FC16 from Newport Corporation, Irvine, CA, and Model #MOFI6CW100000 from E-Tek Dynamics, San Jose, CA, respectively.
- a second enabling technology for the improved efficiency OCDR/OCT designs disclosed in this application is the use of dual-balanced (differential) detection of optically heterodyned signals. Dual-balanced detection is useful when two optical signals with approximately equal DC power, but with AC components which are 180° out of phase, are both present. This is the case, for example, in previously published transmissive implementations of OCDR and OCT which employ a Mach-Zehnder interferometer configuration 60 as illustrated in Fig. 5 .
- the low-coherence source light 62 is incident on the first beamsplitter 64, which splits the light evenly between sample 66 and reference 68 arms.
- the reference arm 68 includes a variable optical delay 70, while the sample arm 66 includes an optical element or sample 72 which is illuminated in transmission.
- Light from the sample and reference arms is recombined in the second beamsplitter 74, and the resulting mixed light is split evenly between two detectors D1 and D2 whose responsivity is carefully matched.
- These detectors D1 and D2 are placed in an electronic circuit 76 whose output 78 is equal to the amplified difference between the photocurrents produced by the two detectors. This detection scheme has two advantages.
- the envelope of difference signal between the two detector currents (as the reference delay is scanned) is equal to twice the amplitude of the AC component of the photocurrent of each detector.
- This excess noise will be eliminated by the difference operation. This detection scheme depends upon careful matching of the DC component of the light power incident on each detector as well as the careful matching of the responsivities of both detectors to be effective, although self-balancing detectors which include self-adjusting variable gains for the two detectors arc commercially available.
- An example of high sensitivity auto-balancing photodetector suitable for use at low frequencies in the designs disclosed in this application is Model #2007 from New Focus Corporation, of Santa Clara. CA, and a balanced receiver suitable for high-frequency applications is Model #1607, from the same vendor.
- the final technology which is different from most previous implementations for OCDR and OCT which is desirable for the novel high-efficiency embodiments is single-mode fiber optic couplers or beamsplitters with splitting ratios other than 50/50.
- unbalanced couplers we will denote such "unbalanced" couplers as having a splitting ratio of ⁇ , indicating that the fraction ⁇ of the light power incident on port I1 is transmitted to port O2, while the fraction (1- ⁇ ) of the light power incident on port I1 is transmitted to port O1, and so on.
- Such unbalanced beamsplitters are very commonly commercially available in the fiber optic marketplace.
- the background design illustrated in Fig. 6 uses an interferometer configuration 100 similar to the Mach-Zehnder illustrated in Fig. 5 , except that both couplers or beamsplitters 102 and 104 may be unbalanced.
- an unbalanced singlemode coupler 102 splits light from the source 106 and sends most of the source light power to the sample arm 108 of the interferometer 100.
- the splitting ratio of the unbalanced coupler 102 is selected such that the amount of power directed into the reference arm 110 is within the suitable range for shot-noise limited detection.
- An optical circulator 112 directs the sample arm light onto the sample 114, and directs light returning from the sample into a second singlemode coupler 104, which in general may also be unbalanced.
- a second optical circulator 116 directs reference arm light onto a variable reference delay element 118, and directs light returning from the delay 118 into the other input port of second single mode coupler 104.
- This configuration places most of the source light on the sample 114. thus automatically eliminating the power loss in the conventional interferometer due to purposeful attenuation of reference arm light to achieve shot-noise limited detection.
- this configuration directs all of the light returning from the sample 114 to a detector 120.
- the expression for the signal-to-noise ratio is given as Eq.
- the interferometer 130 illustrated in Fig. 7 is similar to that illustrated in Fig. 6 , except that the expense of one of the optical circulators is avoided by use of a transmissive delay element 132 rather than a reflective reference ann delay.
- the transmissive delay element 132 could be similar to element 70 illustrated in Fig. 5 . All other advantages of the background design preserved.
- Interferometer 130 will be the preferred embodiment when implementation of a transmissive delay line is practical, such as in recently published high-speed OCT systems which use a novel reference delay based on Fourier transform pulse shaping techniques, which are readily amenable to implementation in a transmissive geometry.
- the interferometer 140 illustrated in Fig. 8 is also similar to the background design of Fig. 6 , except that interferometer 140 avoids the additional expense of one optical circulator while still using a reflective reference delay 118.
- This embodiment preserves all of the advantages of the background design, except that the gain in dynamic range as compared to the conventional system is slightly less, because the optimal value of the first coupler 102 splitting ratio is somewhat smaller than in the background design in order to compensate for the small amount of reference arm power which is returned to the source 106 rather than placed on a detector.
- Interferometer 140 will be the preferred one when a slight loss in efficiency is worth the savings of the cost of one optical circulator.
- the expression for the signal-to-noise ratio is the same as Eq. (3).
- the expression for the optimal splitting ratio for the first coupler 102 which ensures that there is sufficient reference arm power to allow for shot-noise limited detection, but at the same time places the maximum power on the sample 114, under the assumption that ⁇ 1 is small, is the same as given in equation (7).
- This alternative form of interferometer 140 eliminates the expense of the second matched detector D2 and the associated differential gain electronics.
- the expression for the signal-to-noise ratio is the same as Eq. (5).
- the interferometer 150 illustrated in Fig. 9 is similar to the conventional Michelson interferometer arrangement, except that an optical circulator 152 is placed between the low-coherence source 106 and the fiber coupler or beamsplitter 154 and the beamsplitter 154 is unbalanced.
- the splitting ratio of the unbalanced coupler 154 is selected such that the amount of power directed into the reference arm 156 is small enough to allow for shot-noise limited detection, but large enough to avoid thermal detector noise.
- the optical circulator 152 directs most of the light reflected from the sample 114 but only a small fraction of the light returning from the reflective reference delay element 118 onto the detector 156. Only a single detector 156 is needed in this configuration.
- This interferometer configuration places most of the source light on the sample 114, thus automatically eliminating the power loss in the conventional interferometer due to purposeful attenuation of reference arm light to achieve shot-noise limited detection. Secondly, most of the light returning from the sample is directed to the detector 156, thus only a small fraction of the reflected sample arm light is lost to reciprocal losses as in the conventional design.
- the interferometer 160 illustrated in Fig. 10 is similar to that illustrated in Fig. 9 , except that a balanced coupler 162 is used in place of the unbalanced coupler 154 in Fig. 9 , and a dual-balanced detector arrangement 164 is also used.
- This interferometer configuration docs not have the advantage of placing most of the source light on the sample, thus it will not be the preferred embodiment when the source power is sufficient to preclude shot-noise limited detection.
- this interferometer configuration avoids both sample and reference arm reciprocal losses by placing all of the light reflected from the sample and reference arms 158 and 156 on a detector 164, and achieves again in dynamic range of a factor of approximately 1.45 (1.60 dB) as compared to the conventional arrangement. This will be the preferred embodiment when a low-power source is used and the expense of an unbalanced coupler must be avoided.
- the primary commonality between the interferometer configurations is the use of at least one nonreciprocal optical element (preferably an optical circulator) which results in increased efficiency.
- a nonreciprocal optical element preferably an optical circulator
- interferometer configurations in accordance with the present invention could be constructed with a relatively low efficiency (an efficiency similar to that of traditional systems).
- Each of the various embodiments described provides an interferometer system including an optical radiation source, a first optical circulator and an optical detector, A first optical path extends from the optical radiation source, through a first portion of the first optical circulator to a sample location, and from the sample location through a second portion of the optical circulator to the optical detector.
- the interferometer system also includes a first beamsplitter positioned between the optical radiation source and the optical circulator along the first optical path, and a second beamsplitter positioned between the optical circulator and the optical detector along the first optical path.
- the interferometer system includes a second optical path extending from the optical radiation source, through the first portion of the optical circulator to a reference location, from the reference location through the second portion of the optical circulator to the optical detector.
- the optical detector comprises first and second optical detectors, the first optical detector positioned at the end of the first optical path, and the interferometer further includes a second optical path extending from the optical radiation source, through the first portion of the optical circulator to a reference location, from the reference location to the second optical detector.
- ⁇ is the detector responsivity.
- P r is the optical power incident on the photodetector reflected from the reference arm of the interferometer
- P s is that portion of the optical power incident on the photodetector having been backscattered from the sample that is coherent with the reference light
- P x is the optical power incident on the photodetector reflected from the sample arm of the interferometer which is incoherent with the reference light.
- k 0 is the center wavenumber of the optical source
- ⁇ l is the optical path difference between the reference and sample arms.
- noise sources in terms of the photocurrent variance ⁇ i 2 .
- the noise sources to be included in this analysis are receiver noise ⁇ rc 2 , shot noise ⁇ sh 2 , and excess intensity noise ⁇ er 2 .
- Receiver noise may be modeled as thermal noise in a resistance-limited receiver with an effective load resistance R eff .
- the photocurrent variance due to receiver noise can be calculated directly from the manufacturer specifications.
- the random arrival of photons from a monochromatic light source is a Poisson process.
- the random arrival of photons from a broadband, incoherent light source is a Bose-Einstein process.
- the resulting photocurrent variance has two terms: shot noise, and excess photon noise.
- ⁇ ⁇ v ⁇ / 2 ⁇ ln 2 ⁇ c ⁇ ⁇ ⁇ ⁇ FWHM / ⁇ 0 2 , where c is the speed of light, ⁇ FWHM is the full-width half-maximum wavelength bandwidth of the source, and ⁇ 0 is the center wavelength.
- This expression for excess photon noise represents the minimum expected intensity noise for a source with a given effective linewidth.
- Some broadband optical sources, such as mode-locked femtosecond lasers exhibit more than this minimum intensity noise.
- ⁇ ex 2 RIN ⁇ I dc 2 ⁇ B .
- RIN relative intensity noise
- RIN relative intensity noise
- ⁇ i 2 ⁇ rc 2 + ⁇ sh 2 + ⁇ ex 2 .
- excess intensity noise is largely cancelled.
- noise sources that are generated in an OCT system include flicker (1/f) noise, dark current noise, and quantization noise.
- Flicker noise is avoided simply by ensuring a high enough signal carrier (heterodyne) frequency such that the signal bandwidth is well above dc (several kHz is sufficient).
- Dark current noise is the shot noise arising from the detector dark current. It is generally small, and because it is independent of incident light intensity, it is suppressed by the identical method as suppressing receiver noise, that is, allowing sufficient light on the detector such that shot noise dominates.
- Quantization noise arises from an insufficient number of A/D bits sampling the signal.
- noise floor should be less than 1 ⁇ 2 of the least significant bit
- conditioning the signal such that it fills the A/D dynamic range. Because these noise sources can be suppressed or avoided, they are not included in this SNR model.
- the typical OCT configuration is a standard Michelson interferometer (Fig. 1a).
- P r P 0 R r /4
- P s P 0 R s /4
- P x P 0 R s /4
- P 0 is the power output of the optical source
- R r , R s , and R x are the power reflectivities of the reference ODL, coherent backscattering from the sample, and the incoherent scattering from the sample arm optics, respectively.
- the optimum splitting ratio depends on the properties of the optical source, photodetectors, and delay line.
- An explicit expression for the optimum splitting ratio could by obtained analytically by maximizing the SNR, or alternatively, the modeled SNR could be plotted and the optimum splitting ratio can simply be read from the plot.
- the background design illustrated in figure 6 can also be implemented with an unbalanced second coupler and a single detector.
- P r P 0 ⁇ R r ⁇ ⁇ 1 ⁇ ⁇ 2 ⁇ T c 2
- P s P 0 ⁇ R s ⁇ 1 - ⁇ 1 ⁇ 1 - ⁇ 2 ⁇ T c 2
- P x P 0 ⁇ R x ⁇ 1 - ⁇ 1 ⁇ 1 - ⁇ 2 ⁇ T c 2
- ⁇ 1 is the splitting ratio of the first coupler
- ⁇ 2 is the splitting ratio of the second coupler.
- P r P 0 T r ⁇ 1 ⁇ 2
- P s P 0 ⁇ R s ⁇ 1 - ⁇ 1 ⁇ 1 - ⁇ 2 ⁇ T c 2
- P x P 0 ⁇ R x ⁇ 1 - ⁇ 1 ⁇ 1 - ⁇ 2 ⁇ T c 2
- ⁇ 1 is the splitting ratio of the first coupler
- ⁇ 2 is the splitting ratio of the second coupler.
- P r P 0 R r ⁇ 1 ⁇ 2 ( 1- ⁇ 1 )
- P s P 0 ⁇ R s ⁇ 1 - ⁇ 1 ⁇ 1 - ⁇ 2 ⁇ T c 2
- P x P 0 ⁇ R x ⁇ 1 - ⁇ 1 ⁇ 1 - ⁇ 2 ⁇ T c 2 .
- This embodiment uses an unbalanced splitter and a single detector.
- P r P 0 R r ⁇ 2
- P s P 0 ⁇ R s ⁇ 1 - ⁇ 2 ⁇ T c 2
- P x P 0 ⁇ R x ⁇ 1 - ⁇ 2 ⁇ T c 2
- SNR 2 ⁇ ⁇ 2 ⁇ P 0 2 ⁇ R r ⁇ R s ⁇ ⁇ 2 ⁇ 1 - ⁇ 1 2 ⁇ T c 4 ⁇ re 2 + 2 ⁇ q ⁇ ⁇ ⁇ P 0 ⁇ T c 2 ⁇ R r ⁇ ⁇ 2 + R x ⁇ 1 - ⁇ 1 2 ⁇ B + RIN ⁇ ⁇ 2 ⁇ P 0 2 ⁇ T c 4 ⁇ R r ⁇ ⁇ 2 + R x ⁇ 1 - ⁇ 1 2 2 ⁇
- This embodiment has the significant advantage that an existing fiber-optic Michelson interferometer OCT system can be easily retrofitted with a circulator in the source ann and a balanced receiver with no need to disturb the rest of the system. We have recently demonstrated this embodiment in a high-speed endoscopic OCT system.
- transmissive any sample illumination and collection geometry in which the illumination and collection optics occupy separate optical paths, for example using separate fibers for illumination and collection of light from the sample.
- the path of light through the sample may be in a straight line, in which case the illumination and collection optics would be lined up along a path aimed directly through the sample.
- the path of light through the sample may be transmissive in the sense illustrated in figures 11-13 , in which there is some angle (other than 0 or 180 degrees) between the illumination and collection optical directions.
- OCDR and OCT are in some sense reflective geometries, for the purposes of this description we define them as transmissive so long as separate optical paths are used for illumination and collection.
- OCDR and OCT can be used to form images of the internal structure of biological or other materials.
- non-straight line geometry with any angle other than 0 or 180 degrees between the illumination and collection optics
- OCDR and OCT may be used to probe the internal structure of biological or other materials in cases in which it is not convenient to use a retro-reflection geometry (as in embodiments 1-5).
- retro-reflection geometry as in embodiments 1-5.
- This embodiment is similar in all respects to embodiment 1, except that a transmissive sample is used in the place of the circulator and sample in embodiment 1.
- This embodiment is similar in all respects to embodiment 2, except that a transmissive sample is used in the place of the circulator and sample in embodiment 2.
Abstract
Description
- Optical Coherence Tomography (OCT) is a novel imaging technique which allows for noninvasive cross-sectional imaging in scattering or cloudy media with high spatial resolution and high dynamic range. OCT is a two-dimensional extension of Optical Coherence-Domain Reflectometry (OCDR) which is also commonly referred to as Optical Low Coherence Reflectometry (OLCR), in which a low temporal coherence light source is employed to obtain precise localization of reflections internal to a probed structure along the optic axis. The one-dimensional ranging technique of OCDR/OLCR has previously been utilized for characterization of bulk-, integrated-, and fiber-optic structures, as well as biological tissues. In OCT, this technique is extended to provide for scanning of the probe beam in a direction perpendicular to the optic axis, building up a two-dimensional data set comprising a cross-sectional image of internal tissue backscatter.
- OCT has previously been applied to imaging of biological tissues in vivo and in vitro, although the majority of initial biomedical imaging studies concentrated on transparent structures such as the eye. Initial ophthalmic imaging studies demonstrated significant potential for OCT imaging in routine examination of normal and abnormal ocular structures, including imaging of the cornea, iris, and other structures of the anterior eye; the lens and lens capsule; and numerous structures in the posterior eye, including the neurosensory retina, retinal nerve fiber layer, retinal pigment epithelium, and choroid. In OCT examination of the retina, initial in vivo clinical studies have demonstrated its utility in aiding diagnosis in a variety of vitreoretinal diseases, including macular hole, macular degeneration, detached retina, and glaucoma. Clinical trials of OCT imaging for ophthalmic applications are currently under way at several centers, and a commercial ophthalmic OCT scanner is available from Humphrey Systems of Dublin, California.
- Several recent publications have demonstrated the potential applications of OCT in highly scattering media for the measurement of tissue optical properties and imaging. Optical imaging in scattering media such as biological tissue is in general a very difficult problem, particularly for techniques such as OCT which depend primarily upon unscattered or singly-scattered light for image formation. It has been observed in preliminary studies and theoretical treatments that this singly-scattered gating requirement practically limits OCT imaging to a useful penetration depth of a few millimeters at best in nontransparent human tissues. Nonetheless, several authors have identified diagnostic scenarios in which a technique for improved, non-invasive 10-20-micron scale optical imaging near tissue surfaces has significant potential for clinical utility. These include applications of OCT imaging in skin, teeth, vascular tissues, and gastrointestinal mucosa. The latter two examples are significant since with its fiber optic implementation, OCT is readily adaptable to minimally invasive diagnostic modalities such as catheterization or endoscopy. OCT system implementations featuring the high-speed imaging acquisition necessary for in vivo application and catheter/endoscopic delivery have been reported. The application of OCT to biomedical imaging provides the potential for sub-surface tissue characterization with sufficient resolution to provide microscopic morphological information relevant to pathological diagnosis without the need for biopsy.
- Recent publications have also illustrated the potential applications of OCT for imaging in cloudy or turbid non-biological media in industrial processing in the manufacturing industry. OCT imaging may be useful for on-line process control or product testing and evaluation. Initial experiments have demonstrated OCT imaging in ceramic and other highly scattering materials, as well as for the characterization of the surface topology of opaque industrial materials such as metals (i.e., ball bearings).
- Optical coherence tomography performs micron-scale topographic imaging of internal tissue microstructure using a combination of the principles of low-coherence interferometry and confocal microscopy. Reference is made to
Fig. 1 illustrating anexemplary OCT system 10 in which the tissue to be examined is placed in thesample arm 12 of a Michelson interferometer illuminated by abroadband light source 16. Due to the limited coherence length of the source (typically 10-15 microns), light returning from thereference arm 18 and light backscattered by internal sample reflections interferes constructively or destructively only when the interferometer arm optical path lengths are matched to within the source coherence length. Scanning thereference arm 18 length through a position corresponding to the depth of a reflecting site within the sample generates a localized interference pattern, which is recorded as a localized modulation of the detector current as a function of the reference arm position. Abeamsplitter 20,optical detector 22,transimpedance amplifier 24,demodulator 26, A/D converter 28, anddisplay 30 are also shown. The detector current generated by a sample containing multiple reflecting sites distributed along its depth (such as biological tissue) contains the sum of multiple, overlapping copies of this interference pattern. A map of tissue reflectivity versus depth or "A-Scan" is obtained by scanning thereference mirror 32 at constant velocity, while recording the envelope of the detector current. The envelope may be recorded with high dynamic range by scanning thereference mirror 32 at fixed velocity, and demodulating the detector current at the resulting Doppler frequency. Cross-sectional images of tissue backscatter or "B-Scans" may be acquired by obtaining sequential A-scans while scanning the probe beam across the tissue surface using a lateral beam scanning mirror 33 or some other lateral scanning optic device. The resulting two-dimensional datasets are plotted as gray-scale or false-color images. - A significant advantage of using low-coherence interferometry for signal detection is that the
interferometer 14 acts as an optical heterodyne detector, providing a dramatic expansion in dynamic range compared to direct detection of scattered light. Since the interferometric component of the detector current is proportional to the product of the electric field amplitudes returning from each arm, the detected envelope signal is proportional to the square root of the sample power reflectivity. Extremely faint reflections in the sample (~10-11 times the incident optical power) are routinely detected in A-scans recorded in a fraction of a second. As illustrated inFig. 1 , theinterferometer 14 can also be implemented using inexpensive semiconductor sources and detectors, and flexible single-mode optical fibers suitable for remote imaging through minimally invasive diagnostic instruments. - A significant limitation in the use of OCDR and OCT in highly scattering media is that the OCT probe light is very strongly (exponentially) attenuated in the scattering material, thus limiting the imaging depth which can be achieved in a given amount of time for a given sensitivity. For a conventional OCT system in which a 50/50
beamsplitter 20 is used in the Michelson interferometer, the signal to noise ratio (SNR) of the detected electronic signal in the shot-noise limit is given by Eq. (1) below:
In this expression, SNR is signal-to-noise ratio (a measure of the sensitivity which also relates to imaging depth in scattering media), ρ is the detector responsivity, Ps is the optical power incident on the sample, Rs is the optical power reflectivity of the sample, q is the charge on the electron, and B is the detector bandwidth. The latter variable B is inversely proportional to the time required to obtain an OCDR scan or OCT image. The shot-noise limit under which this expression is calculated is well known to those practiced in the art to be the best possible performance (i.e., to give the best value for S/N) which can be achieved in an optical detection system. Even though not all implementations of OCDR and OCT may actually achieve true shot-noise limited performance and therefore may not be strictly governed by Eq. (1), most implementations aim to be near this limit and the equation is still a useful guideline illustrating the trade-offs between sensitivity, source power, and image acquisition time in this limiting case of the best possible performance. - Equation (1) makes clear that there is a trade-off between sensitivity or depth, imaging time, and the source power incident on the sample in OCDR and OCT. Increases in imaging speed, for example, may only be achieved through either a decrease in S/N or an increase in power incident on the sample. Increases in sensitivity or imaging depth (both proportional to S/N) may only be obtained by increasing either the imaging time or the power on the sample. For industrial and medical imaging applications, it is desirable to image as rapidly as possible, at a rate of at least several images per second. Recently, new technology has been developed permitting OCT image acquisition up to video rate (30 images/second), and high power low-coherence sources have become available to partially compensate for the decrease in sensitivity which necessarily accompanies any increase in imaging speed according to Eq. (1). However, these high power sources are very expensive, and still are not sufficiently powerful to allow for clinically acceptable quality imaging at video rate (or even at the ~10 images/second rate common to ultrasound imaging).
- Two requirements on the amount of optical power which may be incident on the detector must be met in order to be at or near the shot-noise limit in OCDR and OCT. The first requirement is that the total optical power incident on the
detector 22 cannot be arbitrarily high in order for shot noise to dominate over excess intensity noise for available sources. For systems withoptical sources 16 which emit low power, this is not a problem. However, recent developments in source technology have resulted in the availability of higher power sources (10-20 mW) which are very attractive for high-speed imaging since the higher sample arm power partially compensates for the increased bandwidth B necessary for higher speed imaging, according to Eq. (1). Since most industrial and biological samples have very low reflectivity, they do not reflect an appreciable amount of sample arm light power onto thedetector 22. However, in conventional systems employing such high power sources, an attenuator must be placed in thereference arm 18 in order to approach the shot noise limit. This represents a waste of up to 50% of the valuable and expensive source power, which is lost in an attenuator. It would be much better if this power could instead be directed onto the sample, so it could contribute to imaging performance as describe in Eq. (1). Clearly there is a need for an improved interferometer design for OCDR and OCT which avoids power losses due to attenuation required to achieve shot-noise-limited performance on the detector. - The second requirement on the amount of power on the detector is that it must be sufficiently high so that shot noise dominates over thermal noise in the detector. For most commonly available semiconductor detectors in the visible and near-infrared regions of the spectrum, the power on the detector must be at least approximately 1 µW for a typical low speed system using a detector with a bandwidth less than approximately 100 kHz, to 10 µW for a typical high speed system using a detector with a bandwidth of approximately 10 MHz. Thus, there is a range of acceptable power levels which will achieve shot-noise limited performance at the detector, and under the assumption that most of the light reaching the detector comes from the reference arm (i.e., under the approximation of a weakly reflecting sample), this places a limitation on the range of acceptable power levels in the reference arm, which is typically in the range of between 1 µW and 10 µW.
- In conventional OCDR and OCT, the central element of the Michelson interferometer is a
standard beamsplitter 20 which transmits or splits some fraction of the power (typically 50%) of the incident light power into each of the sample andreference arms beamsplitter 20 may be a mirror with a partially reflective coating, while in a fiber optic interferometer the beamsplitter is composed of a pair of fibers partially fused together which is known as a fiber coupler. As illustrated inFig. 2 , the beamsplitter may be abstracted as a four-port optical element with two inputs (labeled as 11 and 12), and two outputs (labeled as O1 and O2). The abstracted beamsplitter illustrated inFig. 2 is characterized by a splitting ratio α, such that a fraction α of the light power incident at port 11 (neglecting small internal losses of the beamsplitter) is transmitted to port O2, while the fraction (1-α) of the light power incident at port I1 is transmitted to port O1. A similar statement applies to light power incident at port I2: in this case, a fraction α of the light power incident at port I2 (neglecting small internal losses of the beamsplitter) is transmitted to port O1, while the fraction (1-α) of the light power incident at port I1 is transmitted to port O2. This conventional beamsplitter is known as a reciprocal optic element because light which is input into either of the output ports O1 or O2 will reciprocally be transmitted to the input ports I1 and I2. Specifically, a fraction α of any light power incident at port O1 is transmitted to port I2, while the fraction (1-α) of the light power incident at port O1 is transmitted to port I1. Finally, a fraction α of any light power incident at port O2 is transmitted to port I1, while the fraction (1-α) of the light power incident at port O2 is transmitted to port I2. - A second clear drawback of the use of the conventional Michelson interferometer topology in OCDR and OCT is that significant reflected sample arm power is lost because it is inevitably directed back into the source, rather than being collected by the
detector 22. In the theoretical analysis which leads to Eq. (1) (derived in the limit of a low reflectivity sample) the noise power is proportional to the amount of power incident on thedetector 22 from thereference arm 18, while the signal power is proportional to the product of the coupler splitting ratios from thesource 16 to thesample arm 12 and from thesample arm 12 to thedetector 22. In the 50/50 (α=0.5) Michelson interferometer used in conventional OCT (seeFigure 1 ), the light from thebroadband source 16 is split evenly between the sample and reference arms, while light returning from both the sample and reference arms is split again into theinput arms source 16 anddetector 22. Thus, the detected signal power is proportional to the product of the 50% splitting ratio from thesource 16 to thesample arm 12, and the 50% splitting ratio from thesample arm 12 to thedetector 22, for a combined sample power double splitting ratio of 25%. Fiber couplers with coupling ratios other than 50% are commonly available; however, their use in the Michelson configuration is even worse. For example, if a 90/10 beamsplitter directs 90% of the source light into the sample arm and only 10% of the light into the reference arm, then the combined sample power splitting ratio is only 9% (10% of the 90% of the source light power incident on the sample). - The modified form of Eq. (1) which is correct for the case of arbitrary splitting ratio is set forth as Eq. (2):
Here, α is the coupler splitting ratio and Po is the source power. Eq. (2) is consistent with Eq. (1) since in the case of Eq. (1), Ps=Po/2. Clearly, the SNR in Eq. (2) is optimized for α=0.5, or a 50% coupling ratio. - Until the development of the present invention, the only method to increase the sensitivity or acquisition rate in OCDR and OCT was to increase the source power. Increases in the source power are very expensive given current source technology. The design of conventional OCDR and OCT interferometers with reciprocal beamsplitters, is very inefficient with the expensive source power, since up to 50% of the source power is lost due to attenuation of the reference arm, and an additional 50% of the power reflected from the sample is wasted by being directed back into the source. An interferometer design which avoids both of these problems could be up to a factor approaching 4 more efficient, and could thus obtain better quality images at the high speeds required for commercial applications of OCDR and OCT technology. Thus, there is a clear need for an invention which makes more efficient use of broadband source light than the conventional OCT interferometer.
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WO 97/32182 A1 Figure 3 an interferometer for OCT based on a Mach-Zehnder interferometer (MZI) design using fiber couplers at the input and output ends. The couplers may be 50/50 couplers or configured to provide an uneven split. An optical circulator is arranged in each arm of the MZI. The circulator in one arm routes the optical path in that arm to a reference mirror and back. The circulator in the other arm routes the optical path in that arm to a sample and back. A dual balanced receiver is arranged at the output of the MZI to collect the signal. - Aspects of the invention are set forth in the appended claims.
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Fig. 1 is a schematic illustration of a traditional OCT system; -
Fig. 2 is a schematic illustration of a reciprocal beamsplitter; -
Fig. 3 is a schematic illustration of an optical circulator, -
Fig. 4 is a schematic illustration of an optical circulator implemented using a polarizing beamsplitter and a Faraday rotator; -
Fig. 5 is a schematic illustration of a Mach-Zehnder interferometer configuration; -
Fig. 6 is a schematic illustration of an example background design of interferometer; -
Fig. 7 is a schematic illustration of an interferometer embodiment according to the invention; -
Fig. 8 is a schematic illustration of another interferometer embodiment according to the invention; -
Fig. 9 is a schematic illustration of another interferometer embodiment according to the invention; -
Fig. 10 is a schematic illustration of another interferometer embodiment according to the invention; -
Fig. 11 is a schematic illustration of another interferometer embodiment according to the invention; and -
Fig. 12 is a schematic illustration of another interferometer embodiment according to the invention. - The invention, which is described in several embodiments, consists of novel interferometer designs for OCDR and OCT which employ non-reciprocal optical elements in order to make more efficient use of the source light power.
- The critical technology which enables the present invention are nonreciprocal optical elements which have recently become commercially available, such as the optical circulator (OC) and Faraday Rotator (FR). An
optical circulator 50, as illustrated inFig. 3 , is a three-port optical device in which all power incident on input port I1 (except for small internal losses) is directed into output port O1 which is common with the second input port I2. All light incident on the input port I2 (except for small internal losses) is similarly directed into the output port O2. Polarization-independent optical circulators are commercially available, in which the performance is independent of the polarization state of the light at the input or output ports. Bulk-optic and fiber-optic versions are commercially available: fiber-optic versions are particularly suitable for use in fiber-optic implementations of OCDR and OCT. An example of a commercially available fiber-optic optical circulator which would be suitable for use in the designs disclosed in this application is Model #60-13-3 from Princeton Optics, Inc., of Ewing, New Jersey. - A second nonreciprocal optical element suitable for use in improving the performance of OCDR and OCT is the Faraday rotator. A Faraday rotator is a device which rotates the polarization state of a light beam which traverses it, by an angle which is a characteristic (fixed or variable) property of the rotator. In particular, a polarization-dependent form of
optical circulator 52 may be constructed from a 45°Faraday rotator 54 and a polarizing beamsplitter (PBS) 56, as illustrated inFig. 4 . Apolarizing beamsplitter 56 is an optical device which either transmits or reflects light incident upon it depending upon the polarization state of the incident light. As illustrated inFig. 4 , vertically polarized light incident on aPBS 56 oriented as illustrated will pass through thePBS 56 and be incident on theFR 54. The rotation state of the light will be rotated by 45° by theFR 54, and may then be directed onto a reflective element orsample 58, which must preserve the polarization state of the light reflected. The reflected light will be rotated another 45° by theFR 54, and will then be reflected by thePBS 56 since its polarization state has been rotated by a total of 90° from that of the incident light. This configuration is effectively a form ofoptical circulator 52. in which the incident light is considered as entering port I1. the transmitted and reflected light transit ports O1 and I2, respectively, and the output light exits port O2. It should be noted that the device illustrated inFig. 4 is just one possible implementation of an optical circulator, and this is not an optimal implementation in many cases because the polarization state of thelight entering port 12 must match the polarization state of the light exiting port O1, thus the sample must preserve polarization. Optical circulators are commercially available which allow for arbitrary polarization states at any of the input ports I1 or I2. Thus, in the remainder of this technical description reference will be made only to optical circulators in general, and not specifically the PBS/FR implementation. However, it should be understood that this implementation may be used whenever the sample does in fact preserve the polarization state of the light reflected from it, and this implementation may in fact be less expensive than the alternative in that case. An example of a polarizing beamsplitter and a Faraday rotator suitable for use in the designs disclosed in this application are Model #10FC16 from Newport Corporation, Irvine, CA, and Model #MOFI6CW100000 from E-Tek Dynamics, San Jose, CA, respectively. - A second enabling technology for the improved efficiency OCDR/OCT designs disclosed in this application is the use of dual-balanced (differential) detection of optically heterodyned signals. Dual-balanced detection is useful when two optical signals with approximately equal DC power, but with AC components which are 180° out of phase, are both present. This is the case, for example, in previously published transmissive implementations of OCDR and OCT which employ a Mach-
Zehnder interferometer configuration 60 as illustrated inFig. 5 . The low-coherence source light 62 is incident on thefirst beamsplitter 64, which splits the light evenly betweensample 66 andreference 68 arms. Thereference arm 68 includes a variableoptical delay 70, while thesample arm 66 includes an optical element orsample 72 which is illuminated in transmission. Light from the sample and reference arms is recombined in thesecond beamsplitter 74, and the resulting mixed light is split evenly between two detectors D1 and D2 whose responsivity is carefully matched. These detectors D1 and D2 are placed in anelectronic circuit 76 whoseoutput 78 is equal to the amplified difference between the photocurrents produced by the two detectors. This detection scheme has two advantages. First, since the light intensity incident on each detector surface as a function of reference arm delay is 180° out of phase, the envelope of difference signal between the two detector currents (as the reference delay is scanned) is equal to twice the amplitude of the AC component of the photocurrent of each detector. Secondly, since any excess noise present in the light propagating through the interferometer will be common to both detectors, this excess noise will be eliminated by the difference operation. This detection scheme depends upon careful matching of the DC component of the light power incident on each detector as well as the careful matching of the responsivities of both detectors to be effective, although self-balancing detectors which include self-adjusting variable gains for the two detectors arc commercially available. An example of high sensitivity auto-balancing photodetector suitable for use at low frequencies in the designs disclosed in this application is Model #2007 from New Focus Corporation, of Santa Clara. CA, and a balanced receiver suitable for high-frequency applications is Model #1607, from the same vendor. - The final technology which is different from most previous implementations for OCDR and OCT which is desirable for the novel high-efficiency embodiments is single-mode fiber optic couplers or beamsplitters with splitting ratios other than 50/50. In this application, we will denote such "unbalanced" couplers as having a splitting ratio of α, indicating that the fraction α of the light power incident on port I1 is transmitted to port O2, while the fraction (1-α) of the light power incident on port I1 is transmitted to port O1, and so on. Using this notation, the standard 50/50 beamsplitter has α=0.5. Such unbalanced beamsplitters are very commonly commercially available in the fiber optic marketplace. An example of a singlemode fiber coupler with a splitting ratio of 90/10 which is suitable for use in the designs disclosed in this application is
Model # 28CBB 102/001/AS from Melles Griot Corporation, Irvine, CA. Other couplers with arbitrary splitting ratios are available from this and other vendors. - We disclose interferometer configurations which simultaneously avoid the losses associated with reference arm attenuation and with reciprocal power losses in conventional OCDR/OCT. These configurations are illustrated in
Figs. 6-12 . Most of these configurations involve unbalanced splitters. In this disclosure, we first describe the design qualitatively. Then, for each design design equations are provided for optimizing the splitting ratios in order to obtain maximum signal to noise for a given source power and minimum power required by the detector for shot noise-limited performance. Finally, for each design typical values are presented assuming typical values in the design equations. In each interferometer configuration the various optical elements could typically be interconnected using fiber optic technology, but it is recognized that other technologies such as integrated-optic or conventional bulk-optic (i.e. discrete optical elements) could also be used for interconnection of the optical elements. - The background design illustrated in
Fig. 6 uses aninterferometer configuration 100 similar to the Mach-Zehnder illustrated inFig. 5 , except that both couplers orbeamsplitters Fig. 6 , anunbalanced singlemode coupler 102 splits light from thesource 106 and sends most of the source light power to thesample arm 108 of theinterferometer 100. The splitting ratio of theunbalanced coupler 102 is selected such that the amount of power directed into thereference arm 110 is within the suitable range for shot-noise limited detection. Anoptical circulator 112 directs the sample arm light onto thesample 114, and directs light returning from the sample into asecond singlemode coupler 104, which in general may also be unbalanced. In thereference arm 110, a secondoptical circulator 116 directs reference arm light onto a variablereference delay element 118, and directs light returning from thedelay 118 into the other input port of secondsingle mode coupler 104. This configuration places most of the source light on thesample 114. thus automatically eliminating the power loss in the conventional interferometer due to purposeful attenuation of reference arm light to achieve shot-noise limited detection. Secondly, this configuration directs all of the light returning from thesample 114 to adetector 120. thus none of the reflected sample arm light is lost to reciprocal losses as in the conventional design. The intensities incident on the detectors D1 and D2 as a function of reference arm delay are out of phase, so differential detection may be achieved simultaneous with common-mode rejection of excess intensity noise. - If the splitting ratio of the
second splitter 104 is chosen to be 50/50 (i.e., α2=0.5), then equal powers are incident on each of the dual detectors D1 and D2, and true dual-balanced detection may be achieved. In this case, the expression for the signal-to-noise ratio is given as Eq. (3):
where ρ is the detector responsivity, P0 is the optical source power, α1 is the splitting ratio of thefirst singlemode coupler 102, Tc is the transmission through the circulator, Rs is the reflectivity of the sample, q is the electronic charge, and β is the bandwidth of the detection electronics- We also disclose an expression for the optimal splitting ratio for thefirst coupler 102, which ensures that there is sufficient reference arm power to allow for shot-noise limited detection, but at the same time places the maximum possible power on the sample. This expression is given as Eq. (4):
where Rr is the reflectivity of the reference arm delay line. Here, Pmin is the minimum power which must be present at thedetector 120 in order to ensure shot noise dominates receiver noise. Assuming the typical value of Pmin=10µW, the values of Pc=10mW, Tc=0.85, and Rr=0.9, we obtain an optimal splitting ratio for the first coupler of α1=0.0031. Using a coupler with this splitting ratio as thefirst coupler 102 inFig. 6 , and a coupler with the value of α2=0.5 as thesecond coupler 104 provides a signal-to-noise ratio advantage of a factor of 2.88 (or 4.60 dB) over the conventional Michelson OCDR/OCT arrangement. Thus, using this design OCT images could be obtained at the same rate with a factor of 2.88 times better sensitivity, or alternatively at an acquisition rate of 2.88 times faster with the same sensitivity as in conventional OCT. The use of this design with α2=0.5 allows for the maximum possible gain in dynamic range as compared to the conventional design, and provides the highest dynamic range performance , but suffers from the added expense of twooptical circulators - The splitting ratio of the
second splitter 104 may in general be chosen to be any value, however a convenient choice may be to choose a high splitting ratio, for example α2=α1, and then to use only the top detector D1 for signal detection. This alternative form eliminates the expense of the second matched detector D2 and the associated differential gain electronics. In this case, the expression for the signal-to-noise ratio is given as Eq. (5):
where α1=α2 is the splitting ratio of bothcouplers
Under the same assumptions that Pmin = 10 µW, P0= 10 mW, Tc = 0.85, and Rr = 0.9 as stated above, the optimal value of both couplers is then α2=α1=0.039, and the corresponding signal to noise ratio advantage over conventional OCDR/OCT is a factor of 2.67 (or 4.26 dB). - The
interferometer 130 illustrated inFig. 7 is similar to that illustrated inFig. 6 , except that the expense of one of the optical circulators is avoided by use of atransmissive delay element 132 rather than a reflective reference ann delay. Thetransmissive delay element 132 could be similar toelement 70 illustrated inFig. 5 . All other advantages of the background design preserved. The expression for the signal-to-noise ratio in the case of α2=0.5 (dual-balanced detection) is the same as equation (3), in which case the expression for the optimal first coupler splitting ratio is:
Under the assumptions that Pmin=10µW, P0=10mW; Tc=0.85, and Rr=0.9, the optimal value of the first coupler is then α1=0.0022, and the corresponding signal-to-noise ratio advantage over conventional OCDR/OCT is a factor of 2.88 (or 4.59dB), which is identical to the dual-detector version of the background design. The expression for the signal-to-noise ratio in the case of α2=α1 (one detector only) is the same as equation (5); in this case the expression for the optimal coupler splitting ratio is:
In equations (7) and (8), the term Rr represents reference delay line transmission, rather than reflectivity, since a transmissive delay line is used rather than a reflective one. Under the assumptions that Pmin=10µW, P0=10mW, Tc=-0.85, and Rr=0.9, the optimal value of both couplers is then α2=α1=0.033, and the corresponding signal-to-noise ratio advantage over conventional OCDR/OCT is a factor of 2.70 (or 4.31 dB), which is nearly identical to the single-detector version of the background design. The performance advantages for both versions of this embodiment over conventional OCDR/OCT are the same as forinterferometer 100.Interferometer 130 will be the preferred embodiment when implementation of a transmissive delay line is practical, such as in recently published high-speed OCT systems which use a novel reference delay based on Fourier transform pulse shaping techniques, which are readily amenable to implementation in a transmissive geometry. - The
interferometer 140 illustrated inFig. 8 is also similar to the background design ofFig. 6 , except thatinterferometer 140 avoids the additional expense of one optical circulator while still using areflective reference delay 118. This embodiment preserves all of the advantages of the background design, except that the gain in dynamic range as compared to the conventional system is slightly less, because the optimal value of thefirst coupler 102 splitting ratio is somewhat smaller than in the background design in order to compensate for the small amount of reference arm power which is returned to thesource 106 rather than placed on a detector.Interferometer 140 will be the preferred one when a slight loss in efficiency is worth the savings of the cost of one optical circulator. - If the splitting ratio of the
second beamsplitter 104 ininterferometer 140 is chosen to be 50/50 (i.e., α2=0.5), then equal powers are incident on each of the dual detectors D1 and D2, and true dual-balanced detection may be achieved. In this case, the expression for the signal-to-noise ratio is the same as Eq. (3). The expression for the optimal splitting ratio for thefirst coupler 102, which ensures that there is sufficient reference arm power to allow for shot-noise limited detection, but at the same time places the maximum power on thesample 114, under the assumption that α1 is small, is the same as given in equation (7). Thus, the typical value of rhte optimum splitting ratio α1 and the performance advantage of this embodiment over the conventional Michelson arrangement (under the assumption that α1 is small) are exactly the same s for the dual-detector version ofembodiment # 2. The use ofinterferometer 140 with α2=0.5 allows for the second-highest possible gain of all reflective delay embodiments disclosed in dynamic range as compared to the conventional design, and will be the preferred embodiment when a reflective delay element must be used and the expense of a second optical circulator as required ininterferometer 100 ofFig. 6 must be avoided. - The splitting ratio of the
second splitter 104 ininterferometer 140 may in general be chosen to be any value, however a convenient choice may be to choose a high splitting ratio, for example α2=α 1 and then to use only the top detector D1 for signal detection. This alternative form ofinterferometer 140 eliminates the expense of the second matched detector D2 and the associated differential gain electronics. In this case, the expression for the signal-to-noise ratio is the same as Eq. (5). In this case of α2=α1, under the assumption that both α1, and α2 are small, the optimal values for α2, and α1, are the same as given in equation (8). Thus, the typical value for the optimum splitting ratios α2 and α1 and the performance advantage of this embodiment over the conventional Michelson arrangement (under the assumption that both α2 and α1 are small) are exactly the same as the single-detector version ofembodiment # 1. - The
interferometer 150 illustrated inFig. 9 is similar to the conventional Michelson interferometer arrangement, except that anoptical circulator 152 is placed between the low-coherence source 106 and the fiber coupler orbeamsplitter 154 and thebeamsplitter 154 is unbalanced. The splitting ratio of theunbalanced coupler 154 is selected such that the amount of power directed into thereference arm 156 is small enough to allow for shot-noise limited detection, but large enough to avoid thermal detector noise. Theoptical circulator 152 directs most of the light reflected from thesample 114 but only a small fraction of the light returning from the reflectivereference delay element 118 onto thedetector 156. Only asingle detector 156 is needed in this configuration. This interferometer configuration places most of the source light on thesample 114, thus automatically eliminating the power loss in the conventional interferometer due to purposeful attenuation of reference arm light to achieve shot-noise limited detection. Secondly, most of the light returning from the sample is directed to thedetector 156, thus only a small fraction of the reflected sample arm light is lost to reciprocal losses as in the conventional design. - The expressions and typical values for the signal-to-noise ratio and for the optimal coupler splitting ratios for
interferometer 150 are given above as Eqs. (5) and (6), respectively. The performance advantages for this embodiment over conventional OCDR/OCT are the same as for the second implementation (with α2=α1,) of background design ofFig. 6 , i.e. a signal-to-noise advantage of 2.67 (4.26 dB) as compared to conventional OCDR/OCT.Interferometer 150 is a preferred embodiment to the α2=α1, version ofembodiment # 1 , since it achieves the same performance with fewer components, i.e. with only one unbalanced coupler and one optical circulator. - The
interferometer 160 illustrated inFig. 10 is similar to that illustrated inFig. 9 , except that abalanced coupler 162 is used in place of theunbalanced coupler 154 inFig. 9 , and a dual-balanced detector arrangement 164 is also used. This interferometer configuration docs not have the advantage of placing most of the source light on the sample, thus it will not be the preferred embodiment when the source power is sufficient to preclude shot-noise limited detection. However, this interferometer configuration avoids both sample and reference arm reciprocal losses by placing all of the light reflected from the sample andreference arms detector 164, and achieves again in dynamic range of a factor of approximately 1.45 (1.60 dB) as compared to the conventional arrangement. This will be the preferred embodiment when a low-power source is used and the expense of an unbalanced coupler must be avoided. - We disclose a general procedure for optimizing the choice of coupler splitting ratios for those embodiments employing two beamsplitting couplers. This procedure seeks to balance the requirements to place the largest possible fraction of the source power on the sample, while at the same time ensuring that there is sufficient power in the reference arm to ensure shot-noise limited detection for weakly reflective samples. For the background design and
embodiment # 1, this expression is given by equation (9):
Forembodiment # 1, there is no reference arum circulator, so expression (9) applies if Tc is taken to be 1, and Rr is taken to mean reference delay line transmission, rather than reflectivity. According to Eq. (9) there are an infinite number of possible choices for α1, and α2, however the choices α2 =0.5 (i.e., a 50/50 splitting ratio for the second coupler) and α1 = α2 (i.e., the same splitting ratio for both couplers) are particularly useful. Forembodiment# 2, the expression which optimizes the choice of splitting ratios is given by Eq. (10): - As seen from the above embodiments, the primary commonality between the interferometer configurations is the use of at least one nonreciprocal optical element (preferably an optical circulator) which results in increased efficiency. However, although generally undesirable it is recognized that interferometer configurations in accordance with the present invention could be constructed with a relatively low efficiency (an efficiency similar to that of traditional systems).
- Each of the various embodiments described provides an interferometer system including an optical radiation source, a first optical circulator and an optical detector, A first optical path extends from the optical radiation source, through a first portion of the first optical circulator to a sample location, and from the sample location through a second portion of the optical circulator to the optical detector.
- In the embodiments of
Figs. 7-8 , the interferometer system also includes a first beamsplitter positioned between the optical radiation source and the optical circulator along the first optical path, and a second beamsplitter positioned between the optical circulator and the optical detector along the first optical path. In the embodiment ofFig. 9 , the interferometer system includes a second optical path extending from the optical radiation source, through the first portion of the optical circulator to a reference location, from the reference location through the second portion of the optical circulator to the optical detector. In the embodiment ofFig. 10 the optical detector comprises first and second optical detectors, the first optical detector positioned at the end of the first optical path, and the interferometer further includes a second optical path extending from the optical radiation source, through the first portion of the optical circulator to a reference location, from the reference location to the second optical detector. - The forgoing optimization equations were derived assuming shot noise limited detection. This analysis is not adequate in situations where there is appreciable backreflection from the sample arm optics or when the optical source intensity noise exceeds the excess photon noise predicted by the photon arrival statistics given the source bandwidth. In these cases, the following SNR analysis, which is more complete, should be used to optimize the spitting ratio. Note that some notation used hereafter differs from that used in the previous analysis.
- In a dispersionless OCT system, the photocurrent at a detector will in general be given by
We express noise sources in terms of the photocurrentvariance noise
Assuming that the light intensity backscattered from the sample is negligible compared to the reference power, the average, or d.c. photocurrent is given by Idc ≡〈Id 〉 = ρ(Pr + Px ), where the brackets indicate the mean value. Thus, for the case of a single detector, the total photocurrent variance is given by:
If balanced heterodyne detection is used, then excess intensity noise is largely cancelled. Taking into account extra retroreflected power from the sample arm, Px , however, a component of the excess photon noise remains which is called beat noise and is given by
It is important to note that all photocurrent variances have been written in terms of one-sided noise spectral density functions (i.e. integrated over positive frequencies only), and that however demodulation is performed, B is the width of the detection band-pass filter, as opposed to, for example, the cutoff frequency of a demodulation low-pass filter. - Other noise sources that are generated in an OCT system include flicker (1/f) noise, dark current noise, and quantization noise. Flicker noise is avoided simply by ensuring a high enough signal carrier (heterodyne) frequency such that the signal bandwidth is well above dc (several kHz is sufficient). Dark current noise is the shot noise arising from the detector dark current. It is generally small, and because it is independent of incident light intensity, it is suppressed by the identical method as suppressing receiver noise, that is, allowing sufficient light on the detector such that shot noise dominates. Quantization noise arises from an insufficient number of A/D bits sampling the signal. This can be avoided by selecting an A/D converter with a sufficient dynamic range (the noise floor should be less than ½ of the least significant bit), and by conditioning the signal such that it fills the A/D dynamic range. Because these noise sources can be suppressed or avoided, they are not included in this SNR model.
- We define
For a balanced receiver, the total signal photocurrent is the sum of the photocurrent in each detector, so the mean-square signal photocurrent becomes:
From the definition of SNR and from equations (12) and (14), SNR for a single-detector interferometer can be written in terms of Pr, Ps, and Px, which can be specified a given interferometer configuration:
Similarly, from equations (13) and (15), the expression for SNR for a balanced-receiver interferometer configuration can be written: ,
For each interferometer configuration to be discussed, expressions for Pr, Ps, and Px will be specified, and
As described earlier, the typical OCT configuration is a standard Michelson interferometer (Fig. 1a). In this case, Pr = P 0 Rr /4, Ps = P 0 Rs /4, and Px = P 0 Rs /4, where P 0 is the power output of the optical source, and Rr, Rs, and Rx, are the power reflectivities of the reference ODL, coherent backscattering from the sample, and the incoherent scattering from the sample arm optics, respectively. From equation (16), this results in:
From inspection of the expressions, it can be seen that receiver noise power is constant, shot noise power is approximately proportional to Rr, and excess intensity noise power is approximately proportional to - For the background design illustrated in
figure 6 expressions will be derived for the case of a balanced second coupler and balanced differential detection, and for the case of an unbalanced second coupler and a single detector. In the balanced case, for each detector.
The optimization procedure consists of maximizing this expression for SNR as a function of splitting ratio α. The optimum splitting ratio depends on the properties of the optical source, photodetectors, and delay line. An explicit expression for the optimum splitting ratio could by obtained analytically by maximizing the SNR, or alternatively, the modeled SNR could be plotted and the optimum splitting ratio can simply be read from the plot. The background design illustrated infigure 6 can also be implemented with an unbalanced second coupler and a single detector. In this case,
The embodiment illustrated infigure 7 is similar to the background design illustrated infigure 6 , except that a transmissive delay line is used in the reference arm. Consequently, there is no need of a circulator, and no circulator insertion loss associated with the Pr expression. In the balanced detection case, Pr =P0Trα/2,
The embodiment illustrated infigure 7 can also be implemented with an unbalanced second coupler and a single detector. In this case, Pr = P 0 Tr α1α2 ,
In the embodiment illustrated infigure 8 , a retroreflecting ODL is used without the need for a second optical circulator. In the balanced receiver case, for each detector, Pr = P0Rrα(1-α)/2,
The embodiment illustrated infigure 8 can also be implemented with an unbalanced second coupler and a single detector. In this case, Pr = P 0 Rrα 1 α 2 (1-α1),
The embodiment illustrated infigure 9 uses a Michelson interferometer efficiently by introducing an optical circulator into the source arm instead of the sample arm, as in the previous embodiments. This embodiment uses an unbalanced splitter and a single detector. Here, Pr = P 0 Rrα 2 ,
The embodiment illustrated infigure 10 utilizes a balanced receiver. Here, for each detector,
It must be noted that this embodiment uses a single balanced coupler and therefore there is no optimization required beyond balancing the detectors. This embodiment has the significant advantage that an existing fiber-optic Michelson interferometer OCT system can be easily retrofitted with a circulator in the source ann and a balanced receiver with no need to disturb the rest of the system. We have recently demonstrated this embodiment in a high-speed endoscopic OCT system. - There are many practical applications for using OCDR and OCT to image transmissive samples, rather than reflective samples. Here we define transmissive as any sample illumination and collection geometry in which the illumination and collection optics occupy separate optical paths, for example using separate fibers for illumination and collection of light from the sample. The path of light through the sample may be in a straight line, in which case the illumination and collection optics would be lined up along a path aimed directly through the sample. Alternatively, the path of light through the sample may be transmissive in the sense illustrated in
figures 11-13 , in which there is some angle (other than 0 or 180 degrees) between the illumination and collection optical directions. Although these latter configurations are in some sense reflective geometries, for the purposes of this description we define them as transmissive so long as separate optical paths are used for illumination and collection. In the straight-line geometry (with an angle of 180 degrees between the illumination and collection optics), OCDR and OCT can be used to form images of the internal structure of biological or other materials. In the non-straight line geometry (with any angle other than 0 or 180 degrees between the illumination and collection optics), OCDR and OCT may be used to probe the internal structure of biological or other materials in cases in which it is not convenient to use a retro-reflection geometry (as in embodiments 1-5). There may be other compelling reasons to use an off-axis illumination/collection geometry, for example such geometries may be especially sensitive to internal features of the structure of the sample (e.g., cell nucleus sizing in biological tissues). - We disclose two further embodiments (embodiments 5 through 6, illustrated in
figures 11-12 , respectively) which are similar in many respects toembodiments 1 through 2, respectively, except that they are designed to accommodate samples which are transmissive rather than reflective. - This embodiment is similar in all respects to
embodiment 1, except that a transmissive sample is used in the place of the circulator and sample inembodiment 1. - Under the assumption of shot-noise limited detection, the expressions for SNR of this embodiment using dual-balanced and single-detector configurations are also given by equations (3) and (5), respectively, under the conditions that Tc=1 (since there is no circulator in embodiment 5) and that Rs is interpreted as the transmission of the sample rather than its reflectivity. The optimal splitting ratios for the first unbalanced coupler and for both unbalanced couplers using dual-balanced and single-detector configurations are given by equations (7) and (8), respectively, under these same conditions.
- Under the assumption that the more sophisticated signal-to-noise ratio analysis must be used, the expressions for SNR of this embodiment using dual-balanced and single-detector configurations are given by equations (21) and (22), respectively, again under the conditiods that Tc =1 (since there is no circulator in embodiment 7) and that Rs is interpreted as the transmission of the sample rather than its reflectivity. The procedures for optimizing the splitting ratios for the first unbalanced coupler and for both unbalanced couplers using dual-balanced and single-detector configurations are the same as described for the reflective sample configurations immediately following equations (21) and (22), respectively.
- This embodiment is similar in all respects to
embodiment 2, except that a transmissive sample is used in the place of the circulator and sample inembodiment 2. - Under the assumption of shot-noise limited detection, the expressions for SNR of this embodiment using dual-balanced and single-detector configurations are also given by equations (3) and (5), respectively, under the conditions that Tc =1 (since there is no circulator in embodiment 8) and that Rs is interpreted as the transmission of the sample rather than its reflectivity. The optimal splitting ratios for the first unbalanced coupler and for both unbalanced couplers using dual-balanced and single-detector configurations are given by equations (7) (under the assumption that α1 is small) and (8) (under the assumption that both α1 and α2 are small), respectively, under these same conditions.
- Under the assumption that the more sophisticated signal-to-noise ratio analysis must be used, the expressions for SNR of this embodiment using dual-balanced and single-detector configurations are given by equations (23) and (24), respectively, again under the conditions that Tc =1 (since there is no circulator in embodiment 6) and that Rs is interpreted as the transmission of the sample rather than its reflectivity. The procedures for optimizing the splitting ratios for the first unbalanced coupler and for both unbalanced couplers using dual-balanced and single-detector configurations are the same as described for the reflective sample configurations immediately following equations (23) and (24), respectively.
Claims (15)
- An interferometer for use in an OCDR or OCT imaging system, comprising:a low coherence optical radiation source (106);a first beamsplitter (102) having a first input connected to receive optical radiation from the low coherence optical radiation source;a nonreciprocal optical element (112) having a first input connected to receive optical radiation from a first output of the first beamsplitter, a first output for directing optical radiation from the first input to a sample (114) to be imaged, a second input connected in common with the first output for receiving optical radiation reflected by the sample, and a second output for receiving optical radiation from the second input;a second beamsplitter (104) having a first input connected to receive optical radiation from the second output of the nonreciprocal optical element; andan optical radiation detector (120) connected to receive optical radiation from the second beamsplitter, characterised by:a transmissive delay element (132) having an input connected to receive optical radiation from a second output of the first beamsplitter, and an output connected to a second input of the second beamsplitter.
- An interferometer for use in an OCDR or OCT imaging system, comprising:a low coherence optical radiation source (106);a first beamsplitter (102) having a first input connected to receive optical radiation from the low coherence optical radiation source;a nonreciprocal optical element (112) having a first input connected to receive optical radiation from a first output of the first beamsplitter, a first output for directing optical radiation from the first input to a sample (114) to be imaged, a second input connected in common with the first output for receiving optical radiation reflected by the sample, and a second output for receiving optical radiation from the second input;a second beamsplitter (104) having a first input connected to receive optical radiation from the second output of the nonreciprocal optical element; andan optical radiation detector (120) connected to receive optical radiation from the second beamsplitter,characterised in that a second output of the first beamsplitter is connected for directing optical radiation onto a reference delay element (118) and for receiving optical radiation reflected from the reference delay element, a second input of the first beamsplitter connected for directing optical radiation to a second input of the second beamsplitter.
- The interferometer of claim 1 or 2 wherein the optical radiation detector comprises first and second optical radiation detectors (D1 D2), the first optical radiation detector connected to receive optical radiation from the first output of the second beamsplitter and the second optical radiation detector connected to receive optical radiation from a second output of the second beamsplitter.
- The interferometer of claim 3 wherein the first optical radiation detector and second optical radiation detector are connected to form a differential detector.
- The interferometer of any of claims 1 to 4 wherein the first beamsplitter is an unbalanced beamsplitter which delivers at least 85% of the optical radiation received at the first input to the first output.
- An interferometer for use in an OCDR or OCT imaging system, comprising:a low coherence optical radiation source (106);a nonreciprocal optical element (152) having a first input connected to receive optical radiation from the low coherence optical radiation source and a combination first output/second input; andan optical radiation detector connected to receive optical radiation from a second output of the nonreciprocal optical element; characterised by:a beamsplitter (154) having a first input connected to the combination first output/second input of the nonreciprocal optical element, having a first output connected for directing optical radiation to a sample (114) to be imaged and for receiving reflected optical radiation from the sample to be imaged, and having a second output connected for directing optical radiation to a reference delay element (118) and for receiving reflected optical radiation from the reference delay element.
- The interferometer of any of claims 1 to 6 wherein the beamsplitter comprises an unbalanced beamsplitter.
- The interferometer of claim 6 wherein the optical radiation detector comprises a first optical radiation detector connected to receive optical radiation from a second output of the nonreciprocal optical element and a second optical radiation detector connected to receive optical radiation from a second input of the beamsplitter.
- The interferometer of claim 8 wherein the beamsplitter comprises a balanced beamsplitter.
- The interferometer of any of claims 3, 4, 8 or 9 wherein the first optical radiation detector and second optical radiation detector are connected to form a differential optical radiation detector.
- The interferometer of any of claims 1 to 10 wherein the nonreciprocal optical element comprises an optical circulator.
- The interferometer of claim 11 wherein the optical circulator comprises a Faraday rotator and a polarizing beamsplitter.
- A method of performing OCDR or OCT imaging of a sample, comprising the steps of:(a) producing low coherence optical radiation;(b) directing at least some of the low coherence optical radiation through an optical circulator to the sample by passing the low coherence optical radiation produced in step (a) through a first beamsplitter to the optical circulator, and through a first portion of the optical circulator to the sample;(c) reflecting at least some of the low coherence optical radiation off of the sample;(d) detecting at least some of the reflected low coherence optical radiation and producing an electrical signal corresponding thereto; and(e) directing at least some of the reflected low coherence optical radiation through a second portion of the optical circulator to a second beamsplitter, and from the second beamsplitter to an optical detector for performing step (d); characterised by:(f) directing at least some of the optical radiation produced in step (a) through the first beamsplitter to a transmissive delay element (132), and through the transmissive delay element to the second beamsplitter.
- A method of performing OCDR or OCT imaging of a sample, comprising the steps of:(a) producing low coherence optical radiation;(b) directing at least some of the low coherence optical radiation through an optical circulator to the sample by passing the low coherence optical radiation produced in step (a) through a first beamsplitter to the optical circulator, and through a first portion of the optical circulator to the sample;(c) reflecting at least some of the low coherence optical radiation off of the sample;(d) detecting at least some of the reflected low coherence optical radiation and producing an electrical signal corresponding thereto; and(e) directing at least some of the reflected low coherence optical radiation through a second portion of the optical circulator to a second beamsplitter, and from the second beamsplitter to an optical detector for performing step (d); characterised by:(f) directing at least some of the optical radiation produced in the step (a) through the first beamsplitter to a reference element;(g) reflecting at least some of the low coherence optical radiation from the reference element; and(h) directing at least some of the low reflected low coherence optical radiation of step (g) back through the first beamsplitter and into the second beamsplitter.
- A method of performing OCDR or OCT imaging of a sample, comprising the steps of:(a) producing low coherence optical radiation;(b) directing at least some of the low coherence optical radiation through an optical circulator (152) and then through a first output of a beamsplitter (154) to the sample (114);(c) reflecting at least some of the low coherence optical radiation off of the sample back through the beamsplitter to the optical circulator;(d) directing at least some of the reflected low coherence optical radiation of step (c) back through the optical circulator to an optical detector;(e) directing at least some of the low coherence optical radiation produced in step (a) through the optical circulator and then through a second output of the beamsplitter to a reference element (118);(f) reflecting at least some of the low coherence optical radiation from the reference element back through the beamsplitter to the optical circulator;(g) directing at least some of the reflected low coherence optical radiation of step (f) back through the optical circulator to the optical detector; and(h) detecting with the optical detector at least some of the reflected low coherence optical radiation received from the optical circulator and producing an electrical signal corresponding thereto.
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